KR101931148B1 - Artificial dental prosthesis and method for manufacturing the same - Google Patents

Abstract

One aspect of the present invention relates to an artificial dental prosthesis that is coupled to an abutment (1) provided with a conical linkage (1a) extended outwardly. The artificial dental prosthesis includes a body (10) having a shape corresponding to a lost tooth, a screw hole (20) penetrating the center of the body (10) to guide coupling with the abutment (1), and a mounting hole (30) connected to the screw hole (20) and inserted into the linkage (1a). The mounting hole (30) guides a fitting section (31) fitted into the linkage, and an extension section (35) which is inclined downward to guide the alignment of the linkage (1) on the center line and prevents breakage due to deformation in the coupling process. It is possible to ensure assembly and precision.

Description

TECHNICAL FIELD [0001] The present invention relates to an artificial dental prosthesis,

The present invention relates to an artificial dental prosthesis coupled with an abutment provided with a conical linkage extending outwardly, and a method of manufacturing the artificial dental prosthesis, and more particularly, to an artificial dental prosthesis having a mounting hole, which is coupled with an abutment, The present invention relates to an artificial dental prosthesis and a method of manufacturing the artificial tooth dental prosthesis. The artificial tooth dental prosthesis is manufactured by a process that can improve the workability of the mounting hole and minimize the error.

Generally, an implant is widely used in recent years because it can obtain sufficient strength and aesthetics similar to natural teeth when an artificial tooth is completed after a procedure. Such an implant may be composed of a fixture fixed to the alveolar bone, an abutment connecting the fixture and the prosthesis, and a crown constituting the contour of the prosthesis.

Here, the abutment serves to transfer the applied load through the prosthesis to the jawbone through the fixture. In order to do this, the size, shape and shape of the prosthesis should be considered when machining abutments. In addition, the occlusion with surrounding teeth (upper or lower teeth), gingival status and gum line should be reflected. Therefore, the abutment is customized through the CAD / CAM system considering the individual characteristics of the patient.

On the other hand, the abutment relies on the bonding process in integrating with the prosthesis, and therefore, there is a fatal problem that can not be detached if post correction is required. That is, after the prosthesis is placed, it is checked whether the angle or shape and the height relative to the teeth are correct or not, and the correction of the prosthesis is determined according to the examination result. If correction is required, the prosthesis must be separated from the combined abutment for correction, but it can not be separated due to bonding.

To solve this problem, Korean Patent Registration No. 10-1768410 (entitled "Removable attaching locking link capable of correcting sub-prosthesis and method of assembling upper prosthesis using the same") is proposed. According to the proposed document, the coupling portion 110 has a sloped path extending from the lower end to the upper end so that the upper end portion of the coupling portion 110 has a larger size than the lower end, . That is, the engaging portion 110 is configured to have an outer diameter D that is formed to be 0.01 to 0.1% larger than the inner diameter D 'of the inlet hole 11 of the upper prosthesis 10.

Accordingly, in order to induce the coupling with the upper prosthesis, a reliable fitting engagement is induced only by the pressing force by the interference fit without any other means or mechanism, and a predetermined assembly means for performing mutual engagement or separation of the implant and the upper prosthesis, It also has the advantage of being easily detached from the upper prosthesis, enabling wider use.

However, in the case of the zirconia ceramic prosthesis 2, since an error of ± 0.04 mm occurs due to a shrinkage ratio due to sintering after processing as shown in FIG. 1, the mounting hole 3 is formed more precisely than the connection block 1a of the abutment Is virtually impossible. Therefore, there is a serious problem that the mounting hole 3 of the prosthesis 2 is fractured due to abrupt deformation, as shown in FIG. 2, during the abutment and the forced fitting process.

Korean Patent Registration No. 10-1768410 (entitled "Removable attachment locking link enabling the correction of sub-prosthesis and method of assembling upper prosthesis using the same)

The present invention has been made in order to more positively solve the above problems, and it is an object of the present invention to provide an apparatus and a method for separating a mounting hole, which is combined with an abutment, The present invention provides an artificial dental prosthesis that can be manufactured in a process that can improve the processability of the mounting hole and minimize the error, thereby ensuring overall assembly and precision, and a method of manufacturing the same.

In order to achieve the above object, the present invention provides an artificial dental prosthesis having the following construction.

Wherein the artificial dental prosthesis is coupled with an abutment provided with a conical linkage extending outwardly, the artificial dental prosthesis comprising: a body having a shape corresponding to a lost tooth; and an abutment And a mounting hole communicating with the screw hole at a bottom portion of the upper body to be inserted into the upper connecting rod, wherein the upper mounting hole has a fitting section which is tightly fitted to the connecting rod, And is guided to be aligned in a line, and is divided into an extended section inclined downwardly to prevent breakage due to deformation in the coupling process.

At this time, the upper mounting hole according to the present invention is characterized in that a portion corresponding to 50 to 60% from the upper side to the lower side is set as a dividing base point among the total engaging sections engaged with each other by insertion of the connecting base, And an extended section, respectively.

In addition, the upper fitting section according to the present invention is characterized in that the upper fitting section is formed to have a diameter larger than the minimum diameter of the connecting rod at which the expansion is started and a diameter smaller than the maximum diameter of the connecting rod at which the expansion is finished.

According to an embodiment of the present invention, the upper extension section is inclined at an angle larger than an extension angle of the connector from a division starting point set according to a coupling section to a horizontal plane closed at the bottom, And is formed so as to be located on the same line as the diameter of the first electrode.

In order to accomplish the above object, a method of manufacturing an artificial dental prosthesis according to another aspect of the present invention is as follows.

A method of manufacturing an artificial dental prosthesis, the method comprising: preparing a material for pressurizing at least a zirconium compound into a block, the method comprising: preparing at least a zirconium compound by pressurizing the zirconium compound to form a block, the artificial dental prosthesis being coupled with an abutment provided with a conical linkage extending outwardly; Preliminarily sintering the molded block at 800 to 1300 占 폚 for 30 to 120 minutes; A first sintered block having a shape corresponding to the missing tooth, a screw hole penetrating the center of the upper body to induce fastening with the abutment, and a screw hole communicating with the screw hole at the bottom of the upper body, A cutting forming step of forming a provisional prosthesis by machining a mounting hole coupled with the mounting hole; And a dense sintering step of completing a prosthesis by secondarily sintering the shaped prosthesis at 1400 to 1500 ° C for 100 to 150 minutes.

At this time, the upper cutting-forming step according to the present invention includes a fitting section in which the mounting hole is engaged with the connecting block by interference fit, and a sloping downward sloping portion to guide the upper connecting rod in alignment with the center line, And the upper mounting hole is defined as a division starting point from 50 to 60% from the upper side to the lower side of the total engaging section which is mutually engaged with the insertion of the connecting rod, And the upper extension section is formed to have a diameter larger than the minimum diameter of the connection section where expansion is started and a diameter smaller than the maximum diameter of the connection section to which the expansion is finished and the upper extension section is formed according to the coupling section And is inclined at an angle larger than the expansion angle of the connecting rod from the dividing origin to the horizontal plane closed at the bottom The.

According to the present invention having the above-described constitution, it is possible to provide a press-fit section which is engaged with the fitting hole to be engaged with the abutment, an extension section which guides the abutment to be aligned on the center line, It is also possible to form a zirconia ceramic block constituting the prosthesis by first preliminarily sintering at a low temperature and then performing a second complete sintering process to improve the workability and minimize the error, Thereby providing an effect of ensuring precision.

1 and 2 are cross-sectional views showing a coupling relationship between a conventional prosthesis and an abutment.
Figs. 3 to 5 are sectional views showing a coupling relation between a prosthesis and an abutment according to the present invention; Fig.
FIG. 6 is a flowchart showing the entire method of manufacturing a prosthesis according to the present invention. FIG.

BRIEF DESCRIPTION OF THE DRAWINGS The above and other features and advantages of the present invention will become more apparent from the following description taken in conjunction with the accompanying drawings, in which: FIG.

BRIEF DESCRIPTION OF THE DRAWINGS The advantages and features of the present invention, and how to accomplish them, will become apparent by reference to the embodiments described in detail below with reference to the accompanying drawings. The present invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art. To fully disclose the scope of the invention to those skilled in the art, and the invention is only defined by the scope of the claims. And throughout this specification, like reference numerals refer to like elements throughout.

One aspect of the present invention relates to an artificial dental prosthesis which is coupled to an abutment 1 provided with an outer expanded conical linkage 1a by interference fit, and includes a body 10 having a shape corresponding to a missing tooth as shown in Fig. 3 A screw hole 20 penetrating the body 10 to guide the abutment 1 to the center of the body 10 and a screw hole 20 communicating with the screw hole 20 at the bottom of the body 10, And a mounting hole (30) which is inserted by insertion.

Here, the mounting hole 30 is partitioned into a fitting section 31 and a sloping extension section 35 which are perpendicular to each other as shown in FIG. That is, the fitting section 31 is a portion to which the connecting rod 1a is coupled by interference fit, and the extended section 35 guides the connecting rod 1a to be aligned automatically on the center line. .

The mounting hole 30 is formed in such a manner that a portion corresponding to 50 to 60% from the upper side to the lower side is set as the dividing starting point P1 among the total engaging sections mutually engaged by the insertion of the connecting leg 1a, And is divided into an upper section 31 and a lower section 35 by an upper section and a lower section, respectively. Here, the depth of the mounting hole 30 is formed to be equal to or larger than the height of the connecting rod 1a.

For example, when the height of the connecting rod 1a is 1.2 mm, the depth of the mounting hole 30 is 1.2 mm or more, so that the coupling section actually engaged is 1.2 mm. Here, if the fitting section 31 is formed at a depth of 0.3 to 0.5 mm in a state where the fitting section is 1.2 mm, sufficient bonding force can not be exerted therebetween.

On the contrary, if the fitting section 31 is formed to have a depth of 0.72 to 0.9 mm, there is a problem that the distortion is increased due to the narrow expansion section 35 and the fusion is generated. Therefore, it is preferable that the fitting section 31 has a portion corresponding to 50 to 60% from the upper side to the lower side of the total fitting section at a depth of 0.6 mm to 0.72 mm as a dividing origin P1.

At this time, the fitting section 31 is formed to have a diameter D3 which is larger than the minimum diameter D1 of the linkage 1a at which the expansion starts and smaller than the maximum diameter D2 of the linkage 1a at which the expansion is finished . For example, if the minimum diameter D1 of the connecting rod 1a is 2.62 mm and the maximum diameter D2 is 2.72 mm, the diameter D3 of the fitting section 31 should be in the range of 2.63 to 2.71 mm.

In other words, if the diameter D3 of the fitting section 31 is set to 2.63 mm or less, it will cause severe deformation due to the interference fit and cause fracture. If the diameter D3 is 2.71 mm or more, sufficient bonding force can not be exhibited. Therefore, it is preferable that the diameter D3 of the fitting section 31 is formed to be 2.67 mm, which is an intermediate value having a sufficient bonding force and capable of minimizing the deformation.

The extended section 35 is inclined at an angle A2 that is larger than the extension angle A1 of the connecting rod 1a from the dividing point P1 set in accordance with the coupling section to the horizontal surface finished at the bottom. For example, if the extension angle A1 of the connecting rod 1a has 3 degrees, it is preferable that the extension section 35 is formed to have an inclination of 4 degrees or more, which is larger than the extension angle A1.

That is, as the inclination angle A2 of the extension section 35 has an angle less than or equal to the expansion angle A1 of the connecting rod 1a, the strain increases in the coupling process. Conversely, To the center line of the mounting hole 30.

It is therefore preferable to form the intermediate starting point P2 of the extended section 35 so as to be located on the same line as the maximum diameter D2 of the connecting rod 1a whose expansion is finished. If the maximum diameter D2 of the connecting rod 1a is 2.72 mm, the diameter of the intermediate starting point P2 of the oblique line (reference plane) extending from the dividing starting point P1 to the horizontal surface finished at the bottom is made equal to 2.72 mm.

As described above, the dividing starting point P1 and the intermediate starting point P2, which are smaller than the maximum diameter D2 of the connecting rod 1a, can be set to the angle of the extended section 35 5 °) can be derived automatically.

As shown in FIG. 5, the connecting rod 1a is engaged with the first extended section 35 and aligned on the center line, The interference is started from the intermediate starting point P2 to the fitting interval 31, Therefore, it is possible to secure the overall assembly and precision by guiding the detachment from the region where the brittle is weakest from the portion of the prosthesis.

Hereinafter, in order to verify the effect of the artificial dental prosthesis of the present invention, it was analyzed based on the following experiment.

- Experimental method -

The stress and strain were analyzed through the finite element method (FEA) to investigate the effect of the vertical fitting section, the mounting hole formed by the section with the downward inclined extension section, and the mounting hole composed of the vertical fitting section.

The tool used in the experiment is Solidwoks 2018 Simulation, which models the abutments with a cone-shaped extension extending outwards to induce coupling by interference through the library as follows.

- Psalm making -

The prosthesis used in the experiment is composed of a prosthesis (experimental group) of the mounting hole 30 partitioned by the fitting section 31 and the extended section 35 as shown in Table 1 below and a fitting hole 30), and the rest of the prosthesis (control). Here, the fitting section (31) and the extension section (35) of the experimental group and the control group were constructed in the same manner as described above, and the physical properties of the prosthesis and abutment were applied as shown in Table 2 below.

Experimental group Control group

division Abutment Prosthesis material titanium zirconium Yield stress 8.27371e + 0.8 N / m ^ 2 5.9e + 07 N / m ^ 2 Tensile stress 1.05e + 09 N / m ^ 2 3.5e + 08 N / m ^ 2 Modulus of elasticity 1.048e + 11 N / m ^ 2 9.9e + 10 N / m ^ 2 Poisson rain 0.31 0.34 Mass density 4427.78 kg / m ^ 3 6600 kg / m ^ 3 Shear number 4.10238e + 10 N / m ^ 2 3.6e + 10 N / m ^ 2 Thermal expansion coefficient 9e-06 / kelvin 1.1e-05 / kelvin

- Experimental conditions -

The mounting hole 30 of the prosthesis and the abutment 1a of the abutment were set to be fit contact sets and the coefficient of friction between the prosthesis and the abutment was set to 0.1 as follows. Then, the abutment was set as fixed geometry, and a load of 10 kgf was added to the prosthesis downward to be coupled to the abutment, and then the simulation was performed after converting to a Jacobian point 4 point mesh having a size of 0.73 mm.

-Experiment result-

Experimental results were as follows. Experimental group 3.190 N / m ^ 2 and control group 3.287 N / m ^ 2 stresses were generated and experimental group 2.373 N / m ^ 2 and 2.472 N / m ^ 2 strain occurred Respectively. In other words, the experimental group is divided into the insertion section 31 and the extension section 35, so that it can be understood that the stress and strain acting due to the interference fit are lower than those of the control group.

division Experimental group (N / m ^ 2) Control group (N / m ^ 2) Stress 3.190 3.287



result
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Strain 2.373 2.472



result
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Another aspect of the present invention relates to a method of manufacturing an artificial tooth prosthesis that is coupled with an abutment 1 provided with a conical linkage 1a extending outwardly as shown in FIG. 3, (S10), a pre-sintering step (S20), a cutting molding step (S30), and a dense sintering step (S40).

The material preparing step (S10) is a process of pressing at least a zirconium compound into a block. That is, it is preferable to use an alloy containing 90 to 97% by weight of zirconium oxide, 1.0 to 1.5% by weight hafnium oxide, 3.0 to 4.0% by weight of yttrium oxide, 0.01 to 0.1% by weight aluminum, 0.01 to 0.1% by weight of potassium, 0.01 to 0.1% by weight of germanium, 0.1 weight, and the remaining balance of 0.1 to 0.5 weight% of a coloring additive. Then, the prepared compound is molded into a block at a pressure of 100 to 130 MPa in a two-directional pressure die-floating method in a hydraulic press.

The preliminary sintering step S20 is a process of first sintering the molded block at 800 to 1300 占 폚 for 30 to 120 minutes. Preferably, sintering is performed at 1000 to 1100 占 폚 for 60 minutes. That is, at 1000 ° C or lower, the hardness and the anti-dendritic strength are 11 to 12 Hs and 14 to 18 MPa, which causes a relatively weak strength in the subsequent cutting step (S30) , There is a problem that the tool is easily worn due to the relatively high strength of the hardness and the anti-tensile strength of 20 to 26 Hs and 232 to 424 MPa. Therefore, it is preferable to sinter at 1000 to 1100 ° C so that the hardness and the anti-tensile strength have 16Hs and 34 MPa.

The cutting forming step S30 is a process of molding the first sintered block into the shape of the prosthesis. 3, a body 10 having a shape corresponding to a tooth missing a block and a screw hole (not shown) penetrating the body 10 to induce fastening of the abutment 1 to the center of the body 10, And a mounting hole 30 communicating with the screw hole 20 at the bottom of the body 10 and being inserted into the connecting rod 1a.

4, a portion corresponding to 50 to 60% from the upper side to the lower side is set as a dividing origin point P1 of the total engaging section which is interlocked with the insertion of the connecting section 1a as shown in FIG. 4, The upper and lower sides of the starting point P1 are divided and divided into the fitting section 31 and the extending section 35, respectively.

Here, the fitting section 31 is formed to have a diameter D3 which is larger than the minimum diameter D1 of the connecting rod 1a at which the expansion starts and smaller than the maximum diameter D2 of the connecting rod 1a at which the expansion is finished. The extended section 35 is inclined at an angle A2 that is larger than the extension angle A1 of the connecting rod 1a from the dividing point P1 set according to the coupling section to a horizontal plane closed at the bottom.

That is, if the intermediate starting point P2 of the extended section 35 is set so as to be on the same line as the maximum diameter D2 of the connecting rod 1a whose expansion is finished, the inclination angle A2 of the extended section 35 is automatically Respectively. Since the shape conditions of the mounting hole 30 are the same as those described above, a detailed description thereof will be omitted.

In the dense sintering step (S40), the formed prosthesis is secondarily sintered at 1400 to 1500 DEG C for 100 to 150 minutes to complete the prosthesis. That is, the molded prosthesis is sintered at 1450 ° C for 120 minutes, so that the hardness and the anti-stiffness of the finished prosthesis are 12 to 16 Hs and 585 to 683 MPa.

As described above, since the first sintered soft block is processed into the shape of the prosthesis and then subjected to the second complete sintering process, it is possible to minimize the wear due to the tool while having excellent hardness and anti- The error can be remarkably reduced.

Hereinafter, in order to verify the effect of the manufacturing method of the present invention, the following experiment was conducted.

- Experimental method -

The molded block was preliminarily sintered at a temperature of 800 ° C, 1000 ° C, 1100 ° C, 1200 ° C and 1300 ° C for 1 hour, and then each sintered block was sintered for 2 days with a diameter of 3 mm, an inclination angle of 10 °, The prosthesis was dry-formed by upward cutting using a carbide solid type ball end mill. And, for cutting tools, the measurement time was measured to 0.3 mm of margin wear using a measuring software on a digital microscope.

-Experiment result-

First sintering temperature
(° C) Cutting speed
(m / min) Spindle speed
(RPM) Tool life
(min) 800 30 5000 4 1000 30 5000 8 1100 30 5000 18 1200 30 5000 4 1300 30 5000 3

1100 ℃ 1200 ℃

Experimental results As shown in Table 4, the tool life of the tool sintered at 1100 ° C was the longest at 18 minutes in the dry cutting of the pre-sintered block, and the tool life of the tool sintered at 1000 ° C was long at 8 minutes.

As shown in Table 5, when the block sintered at 1200 ° C is processed as shown in Table 5, since the wear rate of the tool is remarkably increased due to the high hardness and the anti-dipping strength, the error rate of the prosthesis is relatively increased.

Therefore, it can be seen that the precision of the prosthesis can be improved only when the second complete sintering is performed after the shape of the prosthesis in the first sintering state at 1100 ° C, considering the time required for processing the single prosthesis.

As described above, according to the present invention, it is possible to form a fitting section to be engaged with the fitting hole engageable with the abutment, and an extended section to guide the abutment to be aligned on the center line and prevent fracture due to deformation in the fitting process As a matter of course, zirconia ceramic blocks forming the prosthesis can be fabricated from the first preliminary sintering process at the low temperature and then the second complete sintering process, thereby improving the workability and minimizing the error, thereby securing the overall assembly and precision. Provides an effect.

1: abutment 1a: connecting rod
10: body 20: screw hole
30: mounting hole 31: fitting section
32: Extended section P1: Division point
P2: intermediate starting point
S10: Steps to prepare the material
S20: preliminary sintering step
S30: Cutting step
S40: dense sintering step

Claims (6)

And an abutment (1) provided with a conical linkage (1a) extended to the outside,
A screw hole 20 penetrating the abutment 1 to guide the abutment 1 to the center of the upper body 10 and a screw hole 20 penetrating the lower body of the upper body 10, And a mounting hole (30) communicating with the screw hole (20) and being inserted into the upper connecting rod (1a) by insertion,
The upper mounting hole 30 guides the fitting section 31 and the upper connecting section 1a to be aligned with the center line in a tight fitting manner with the connecting section 1a. 1. An artificial dental prosthesis which is divided and organized into a photo extension section (35);
The upper mounting hole 30 sets a portion corresponding to 50 to 60% from the upper side to the lower side among the total engaging portions which are mutually engaged with each other by the insertion of the connecting rod 1a as a dividing starting point P1, (31) and an extended section (35) in the upper and lower sides, respectively.
delete The method according to claim 1,
The upper fitting section 31 is formed to have a diameter D3 which is larger than the minimum diameter D1 of the connecting rod 1a at which the expansion starts and smaller than the maximum diameter D2 of the connecting rod 1a at which the expansion is finished Artificial dental prosthesis.
The method of claim 3,
The upper extension section 35 is inclined at an angle A2 that is larger than the extension angle A1 of the connecting rod 1a from the division point P1 set according to the coupling section to a horizontal plane closed at the bottom,
Wherein an intermediate starting point (P2) of the upper extension section (35) is formed so as to be located on the same line as the maximum diameter (D2) of the connecting rod (1a) whose expansion is finished.
(S10) a step of pressing at least a zirconium compound into a block to form a block, the block being connected to the abutment 1 provided with the conical connecting rod 1a extended outwardly; A preliminary sintering step (S20) of first sintering the molded block at 800 to 1300 占 폚 for 30 to 120 minutes; A body 10 having a shape corresponding to the lost teeth of the primary sintered block, a screw hole 20 penetrating the abutment 1 to induce fastening with the abutment 1 at the center of the upper body 10, (S30) for forming a prosthesis by machining a mounting hole (30) communicating with the screw hole (20) at the bottom of the body (10) and being inserted into the upper connecting rod (1a); And a dense sintering step (S40) for sintering the shaped prosthetic material at a temperature of 1400 to 1500 DEG C for 100 to 150 minutes to complete a prosthesis.
The upper cutting-forming step S30 is a step of forming the fitting hole 31 and the upper linkage 1a so that the mounting hole 30 is connected to the connecting rod 1a by interference fit, To prevent breakage, it is divided and organized into a downwardly inclined extension section (35)
The upper mounting hole 30 sets a portion corresponding to 50 to 60% from the upper side to the lower side among the total engaging portions which are mutually engaged with each other by the insertion of the connecting rod 1a as a dividing starting point P1, The upper and lower sides are divided and divided into the fitting section 31 and the extending section 35, respectively,
The upper fitting section 31 is vertically formed to have a diameter D3 which is larger than the minimum diameter D1 of the connecting rod 1a at which the expansion is started and smaller than the maximum diameter D2 of the connecting rod 1a at which the expansion is finished,
Wherein the upper extension section is inclined at an angle A2 that is larger than the extension angle A1 of the connecting rod 1a from the dividing point P1 set according to the coupling section to a horizontal plane closed at the bottom. A method of manufacturing a prosthesis.
delete

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